Connect public, paid and private patent data with Google Patents Public Datasets

Composite prosthesis for preventing post-surgical adhesions

Download PDF

Info

Publication number
US6264702B1
US6264702B1 US09147949 US14794999A US6264702B1 US 6264702 B1 US6264702 B1 US 6264702B1 US 09147949 US09147949 US 09147949 US 14794999 A US14794999 A US 14794999A US 6264702 B1 US6264702 B1 US 6264702B1
Authority
US
Grant status
Grant
Patent type
Prior art keywords
fabric
prosthetic
film
derivative
prosthesis
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
US09147949
Inventor
Francois Régis Ory
Michel Therin
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sofradim Production
Original Assignee
Sofradim Production
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Grant date
Family has litigation

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION, OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/12Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L31/125Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L31/129Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix containing macromolecular fillers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION, OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/08Materials for coatings
    • A61L31/10Macromolecular materials
    • DTEXTILES; PAPER
    • D04BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
    • D04BKNITTING
    • D04B21/00Warp knitting processes for the production of fabrics or articles not dependent on the use of particular machines; Fabrics or articles defined by such processes
    • D04B21/10Open-work fabrics
    • DTEXTILES; PAPER
    • D10INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10BINDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10B2403/00Details of fabric structure established in the fabric forming process
    • D10B2403/01Surface features
    • D10B2403/011Dissimilar front and back faces
    • D10B2403/0112One smooth surface, e.g. laminated or coated
    • DTEXTILES; PAPER
    • D10INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10BINDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10B2403/00Details of fabric structure established in the fabric forming process
    • D10B2403/02Cross-sectional features
    • D10B2403/021Lofty fabric with equidistantly spaced front and back plies, e.g. spacer fabrics
    • D10B2403/0213Lofty fabric with equidistantly spaced front and back plies, e.g. spacer fabrics with apertures, e.g. with one or more mesh fabric plies
    • DTEXTILES; PAPER
    • D10INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10BINDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10B2509/00Medical; Hygiene
    • D10B2509/08Hernia repair mesh

Abstract

Composite prosthesis, comprising a non-absorbable prosthetic fabric and at least one film made of a material which is absorbable in vivo, combined with one surface of the prosthetic fabric. In combination, the prosthetic fabric has a three-dimensional structure separating its two surfaces, at least one of which is open to all post-surgical cell colonization, and the film of absorbable material is linked at least superficially to the other surface of said fabric.

Description

The present invention concerns a composite prosthesis for preventing post-surgical adhesions, in particular in the field of visceral, parietal or neurological surgery. The invention will be described more particularly in relation to a composite prosthesis intended for use in parietal surgery, in the repair of eventrations or hernias.

Post-surgical adhesions include all non-anatomical fibrous connections accidentally induced by a surgical act during the normal process of cicatrization. They may occur in all surgical disciplines regardless of the operation in question. They are generally all the more severe, the greater the surgical trauma and the more affected the tissues which normally ensure the planes of division (interstitial connective tissue, the synovial membranes, the tendon sheaths, peritoneal and pleural serosa, etc.). Any surgical trauma to tissue is followed by a cascade of physiological events, the main times of which can be simplified as follows:

time zero (t0): surgical trauma, capillary invasion;

time zero plus a few minutes: coagulation, formation of fibrin network, release of chemotactic factors;

time zero (t0) plus 12 to 48 hours: influx of leukocytes, predominantly polynuclears;

time zero (t0) plus 24 hours to 5 days: influx of leukocytes, predominantly macrophages;

time zero (t0) plus 4 to 8 days: influx of fibroblasts;

time zero (t0) plus 5 to 14 days: conjunctive differentiation of the cicatricial reaction;

time zero (t0) plus 15 to 180 days: cicatricial remodeling.

Although some of the exact mechanisms are still unknown, particularly as regards determination of the intensity of the reaction, it appears that the first few days are decisive since they condition the influx of fibroblasts responsible for the formation of adhesions.

For this reason, such post-surgical adhesions can provoke syndromes which can be classed principally as chronic pain, occlusive syndromes and female infertility. Furthermore, they increase very substantially the risks of making errors in follow-up surgery (myocardial or intestinal invasion during repeat thoracotomy or laparotomy), while prolonging the operating times, since the preliminary dissection can be very awkward in such cases.

One solution to this problem consists in interposing a physical barrier between the structures which one does not wish to see adhering. However, the desired barrier effect poses the problem of the intrinsic adhesive power of this barrier. The reason is that if the barrier is made of a non-absorbable material, it can itself be the source of adhesions over the course of time; and if it is absorbable, its absorption must be sufficiently non-inflammatory so as not to cause adhesions itself.

Several properties are therefore necessary if a material is to be able to reduce the risk of adhesions, namely, among others:

the material must be substantially smooth and non-porous on at least one of its surfaces, so as not to offer space for cell recolonization;

the surface of the material must limit the original cell adhesion.

Nevertheless, and in particular in visceral and parietal surgery, the barrier must also have a certain mechanical strength allowing it to fulfill its function as an element of surgical reconstruction. Generally speaking, the known prosthetic fabrics, particularly in the treatment of parietal insufficiencies, for example hernias and eventrations, afford an additional mechanical strength to the surgical reconstruction. Such fabrics are all the more effective and their local tolerance is all the better, the earlier and the more intimate their tissue integration. For this reason, the most effective of the known prosthetic fabrics for these indications are generally highly porous and are designed in such a way as to be integrated in the body as rapidly as possible. The term “porous” is intended to signify the characteristic according to which at least one of the surfaces of the fabric is rough, so as to present alveoli, distributed regularly or irregularly, and promoting all cell colonization. It is for this reason that upon contact with the viscera for example, these fabrics promote adhesion, which limits their use at the so-called preperitoneal or retroperitoneal sites. Now, in a number of cases, and more particularly in the case of multiple recurring eventrations, implantation strictly in the preperitoneal site is difficult, even impossible, on account of the existence of an extensive deficit of serosa.

There is therefore a requirement to make available a product which is able to solve the problem of preventing post-surgical adhesions, while at the same time offering a prosthetic reinforcement subject to cell recolonization and tissue integration, and which can be used, for example, to treat an eventration involving substantial peritoneal loss, or small eventrations, by laparoscopy, and hernias.

To this end, patent application WO-A-96/08277 describes a composite prosthesis comprising a prosthetic fabric, in this case an absorbable or non-absorbable lattice, and at least one film made of a crosslinked absorbable collagenous substance, in this case a collagen gel coagulated in the dry state, combined with one surface of the prosthetic fabric. The composite prosthesis thus formed finds an application in the treatment of eventrations and hernias and, according to the inventors, prevents post-operative adhesions because the collagenous membrane constitutes a zone of separation permitting release of any early post-operative adhesions that may develop.

The composite prosthesis according to document WO-A-96/08277 must be improved in respect of the necessary independence, once it is implanted, between, on the one hand, the phenomenon of cell colonization and tissue insertion, which must if possible be directed, and, on the other hand, the absorption of the film, which must be relatively rapid in vivo, in such a way as to limit the phenomena of inflammation.

Such is the object of the present invention.

According to the invention, in combination, on the one hand the prosthetic fabric has a three-dimensional structure separating its two surfaces, at least one of which is open to all post-surgical cell colonization, and, on the other hand, the film of absorbable material is linked at least superficially to the other surface of said fabric.

The term “open surface” is intended to signify that said surface includes alveoli having a certain depth according to the thickness of the three-dimensional fabric, these alveoli passing completely or incompletely through the thickness of the fabric, from one surface to the other. In the case of a complete passage of the alveoli, this will be referred to as an openwork prosthetic fabric or one having an openwork structure.

According to the invention, that surface of the absorbable film opposite the prosthetic fabric is preferably substantially smooth and non-porous.

The absorbable film is preferably made up of at least one polysaccharide derivative forming a hydrogel which is insoluble in aqueous medium.

By virtue of the invention, and in a controllable manner:

the prosthesis prevents immediate post-surgical cell colonization on the side including the absorbable film, which is absorbed during a period of time compatible with the tissue restoration, for example that of the peritoneum;

the prosthesis facilitates the immediate post-surgical cell colonization, on the surface including the fabric, open in such a way as to permit a rapid and mechanically effective integration thereof, in particular when it is used as a parietal or visceral reinforcement.

Preferably, but not exclusively, the prosthetic fabric comprises two opposite porous surfaces, connected to one another by connecting yarns, one of which is open to all post-surgical cell colonization, and the other of which is closed to said colonization by means of the film of absorbable material. For example, the weave of the prosthetic fabric determines, within the thickness of the latter, a multiplicity of alveoli or transverse channels, substantially parallel to one another, opening out on either side of said fabric on the two porous surfaces respectively, and of which the internal section is substantially free of any connecting yarn. This is therefore a flexible prosthetic fabric having a “honeycomb” structure.

Polysaccharide derivative is intended to signify both the polysaccharide considered in the pure state, as well as the latter when chemically modified, or mixed with other biocompatible products or adjuvants.

The polysaccharide is advantageously chosen from the group consisting of mucopolysaccharides, polyanionic polysaccharides, glycosaminoglycans, modified celluloses, and mixtures of these. The polysaccharide derivative is preferably chosen from the group consisting of a derivative of hyaluronic acid (HA) or its salts, a derivative of carboxymethylcellulose (CMC), a derivative of carboxymethylamylose (CMA), a derivative of chondroitin-6-sulfate, a derivative of dermatan sulfate, a derivative of heparin and a derivative of heparin sulfate, or a mixture of these.

Still more preferably, the polysaccharide derivative is a derivative of hyaluronic acid or one of its hyaluronic salts. Hyaluronic acid is a natural mucopolysaccharide which is present, inter alia, in the synovial fluid, in the walls of the blood vessels, the umbilical cord and in other connective tissues. Polysaccharide consists of residues of N-acetyl-D-glucosamine and D-glucuronic acid, connected by β1-3 glucuronide and β1-4 glucosaminide bonds, respectively, in such a way that the structural unit is designated -(1>4)-β-D-G1cA-(1>3)-β-D-GlcNAc. HA dissolves in water and forms a liquid of high viscosity. The molecular weight of HA isolated from natural sources is generally between 5×104 to [sic] 1×107 daltons. As used in the present application, the term “HA” comprises both hyaluronic acid and its hyaluronic salts, and includes, for example, sodium hyaluronate, potassium hyaluronate, magnesium hyaluronate and calcium hyaluronate.

The preferred HA derivative is insoluble in water, and biocompatible, and it can be obtained, for example, by reacting HA with a polyfunctional crosslinking agent, such as a polyfunctional epoxide. Generally speaking, the crosslinking or modifying procedures allowing an HA derivative to be obtained which is suitable for combination with the three-dimensional prosthetic fabric are well known per se and will not be described in detail here. These procedures are described in particular in the patent applications WO-A-89/02445, WO-A-92/00105 and WO-A-92/20349, the contents of these being incorporated in the present patent application as and when necessary.

The thickness of the absorbable film is advantageously less than the thickness of the prosthetic fabric, for example between 2% and 10% of the total thickness of the composite prosthesis, and preferably between about 30 μm and 100 μm, and more preferably about 50 μm to 75 μm.

The absorbable film which forms part of the composite prosthesis of the invention is biocompatible, non-toxic, and is absorbed rapidly in vivo. The absorbable material used can equally well be of animal origin, human origin or synthetic.

In a preferred embodiment, the absorbable film is linked at least superficially to the prosthetic fabric, directly or indirectly, and is preferably linked directly by capillary absorption, within a certain thickness of the material, in the constituent fibers of the prosthetic fabric.

Still more preferably, the absorbable film is linked directly by capillary absorption of the absorbable material in the constituent fibers of the prosthetic fabric over a depth of less than 750 μm, measured from the outer surface of the film.

According to the invention, a composite prosthesis comprises two surfaces which are different in their appearances and functions, namely one surface which is porous or open on one side, in order to accommodate and direct the post-surgical cell colonization, and the other surface is closed for tissue separation without adhesion.

The absorbable film is preferably continuous, smooth and non-porous, entirely covering the prosthetic fabric, and more preferably projects beyond the latter in such a way as to protect the prosthesis from visceral contacts, the overshoot being from 5 to 10 millimeters for example.

The absorbable film is intimately linked to the fabric by surface penetration so as not to constitute a plane of division or delamination, while at the same time maintaining the porosity of the fabric open on the other surface.

The absorbable film is preferably also flexible, in particular in the hydrated state, in such a way as to preserve the manageability of the prosthesis, and its possible use by the celioscopic route.

Once rehydrated, the film restores to the prosthetic fabric its initial mechanical properties (flexibility and elasticity) without fragmenting, and without making the fixation of the prosthesis more difficult. It is additionally transparent, cannot be delaminated and cannot stick when being put into position. Its rapid absorption ensures protection against the initial adhesive phenomena, that is to say in the first week following surgery, or in other words during the period of time necessary for the tissue integration of the opposite surface. Upon its absorption, its weakly inflammatory and/or immunogenic character does not disturb the tissue colonization on the opposite side of said film.

The present invention will be better understood from the detailed description of a preferred embodiment, given by way of example, with reference being made to the attached drawing, in which:

FIG. 1 represents diagrammatically a composite prosthesis according to the present invention;

FIG. 2 represents a diagrammatic sketch of the knitted weave of a prosthetic fabric belonging to a composite prosthesis according to the present invention.

Referring usefully to FIG. 1, a composite prosthesis according to the present invention is designated in a general manner by reference number 1. The prosthesis includes a prosthetic fabric 2 having two surfaces 4 and 5, one of which is covered with a film 3 of polysaccharide derivative. The prosthetic fabric 2 has an openwork three-dimensional structure and thus a certain thickness which separates the surface 4 from the surface 5. This fabric can preferably be a raschel knit formed on a double needle-bed. The spacing of the two needle beds and the delivery speeds of the yarns allow a finished fabric to be obtained in three dimensions (three-dimensional structure), with a thickness of between 1 to [sic] 3 mm, and for example of about 1.8 mm, for a weight of about 90 g/m2. The final characteristics are given independently of the knitting by the choice of basic material employed, for example multiyarn polyester PES 50 dtex, the temperature, and the thermosetting time. Apart from the spinning, the yarn and the fabric do not receive any other treatment (no oiling or washing). Such a fabric has, in accordance with standard NFG 07119, a tensile strength of between about 18 daN and about 30 daN, and a stretch at break of between about 25% to [sic] 37%, in warp, and a tensile strength of between about 9 daN and 15 daN, and a stretch at break of between 60% to [sic] 88%, in weft.

Such a composite fabric can be formed by warp knitting of five layers of yarns, and in accordance with the diagrammatic sketch in FIG. 2. In this figure, each layer of yarns is identified by a letter, ranging from A to E, the sketch itself using a knitting description system which is entirely familiar and comprehensible to the person skilled in the art, and which will not be described in detail here. According to FIG. 2, the preferred prosthetic fabric according to the present invention is, as has already been described, made up of two independent porous surfaces. In the given example, these two surfaces are themselves made up of two layers of yarns, labeled A, B and D, E respectively, the layers A, B giving a surface with tear-shaped openings, in order to accommodate and direct the post-surgical cell colonization, and the layers D, E giving a surface with hexagonal openings which will be closed by the film of collagenous substance. The prosthetic fabric can be knitted on a double-rib raschel loom. In this case, all the bars corresponding to the yarns A, B and D, E are threaded one full/one empty. The layer of connecting yarns is represented by reference C and is threaded full. The different layers A-E of yarns are all knitted at the same time. Thus, the connecting yarns are distributed along the peripheral edges of the openings of each surface and extend substantially perpendicular from one surface to the other surface, preventing connecting yarns from occupying too great a volume of the transverse channels which are formed. The final fabric can then be stabilized simply by heating it at a temperature of between about 170° C. and about 220° C.

It follows from the above description that the yarns making up the three-dimensional fabric are of a non-absorbable but biocompatible nature, hence different than that of the absorbable material of the film.

A composite prosthesis combining a prosthetic fabric of three-dimensional openwork structure, as obtained above, with a film of polysaccharide derivative can be produced in the following way.

The solution containing the polysaccharide derivative is spread uniformly over a plane and hydrophobic inert support to form a resulting film made up of two thin superposed layers. To do this, a first thin layer of the solution is initially applied. After this first thin layer has gelled by means of cooling, a second thin layer of the same solution is applied to its surface.

The prosthetic fabric of three-dimensional openwork structure, having a thickness of the order of 1.8 mm, is applied via its surface with hexagonal openings on the second thin layer, before gelling, so that the fabric anchors in the polysaccharide derivative during the drying of the film. After the reaction, the composite prosthesis is separated from the hydrophobic inert support.

It should be noted that the film of polysaccharide derivative can ascend by capillarity in the fibers, this effect being partly responsible for the high resistance to delamination of the film from the prosthetic fabric. Finally, the film is continuous, and no synthetic fiber originating from the prosthetic fabric appears at its surface. Furthermore, the film has a thickness of the order of 50 μm to 75 μm, but, by capillarity in the fibers of the prosthetic fabric, can reach as far as a thickness of about 750 μm.

Claims (8)

What is claimed is:
1. A composite prosthesis comprising:
a non in vivo-absorbable prosthetic fabric having a weave or knit comprising a three-dimensional structure separating two opposite surfaces, said opposite surfaces connected to one another by connecting yarn, one of said surfaces being porous and open to post-surgical cell colonization, and the other of said surfaces being closed to said colonization;
one film made of at least one polysaccharide derivative hydrogel, which is insoluble in an aqueous medium but absorbable in vivo;
said film having a thickness less than a thickness of the prosthetic fabric; and
said film being linked directly to constituent yarns of the prosthetic fabric by capillary absorption of the polysaccharide derivative in a depth of said prosthetic fabric and into said constituent yarns.
2. A composite prosthesis according to claim 1, wherein the polysaccharide derivative is selected from the group consisting of mucopolysaccharides, polyanionic polysaccharides, glycosaminoglycans, modified celluloses, and mixtures thereof.
3. A composite prosthesis according to claim 1, wherein the polysaccharide derivative is selected from the group consisting of a derivative of hyaluronic acid or one of its hyaluronic salts, a derivative of carboxymethylcellulose, a derivative of carboxymethylamylose, a derivative of chondroitin-6-sulfate, a derivative of dermatan sulfate, a derivative of heparin, a derivative of heparin sulfate, and mixtures thereof.
4. A composite prosthesis according to claims 1, wherein the polysaccharide derivative is a derivative of hyaluronic acid, or one of its hyaluronic salts.
5. A composite prosthesis according to claim 1, wherein said other surface is closed to post-surgical cell colonization into the prosthetic fabric by said film.
6. A composite prosthesis according to claim 5, wherein the weave or knit of the prosthetic fabric comprises within its thickness a multiplicity of alveoli or transverse channels having an internal section free of any connecting yarn, said alveoli or channels being substantially parallel to one another and opening out on either side of said fabric on the two surfaces respectively.
7. A composite prosthesis according to claim 5, wherein the prosthetic fabric has a honeycomb structure.
8. A composite prosthesis according to claim 5, wherein the fabric has an open work structure such as obtained by weaving or knitting on a double rib raschel boom with at least five yarns threaded at the same time, one full and one empty.
US09147949 1997-08-01 1998-07-22 Composite prosthesis for preventing post-surgical adhesions Active US6264702B1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
FR9710102 1997-08-01
FR9710102A FR2766716B1 (en) 1997-08-01 1997-08-01 composite prosthesis for the prevention of post-surgical adhesions and its production process
PCT/FR1998/001624 WO1999006079A1 (en) 1997-08-01 1998-07-22 Composite prosthesis for preventing post-surgical adhesions and method for obtaining same

Publications (1)

Publication Number Publication Date
US6264702B1 true US6264702B1 (en) 2001-07-24

Family

ID=9510103

Family Applications (1)

Application Number Title Priority Date Filing Date
US09147949 Active US6264702B1 (en) 1997-08-01 1998-07-22 Composite prosthesis for preventing post-surgical adhesions

Country Status (6)

Country Link
US (1) US6264702B1 (en)
DE (2) DE69801442D1 (en)
EP (1) EP0998313B1 (en)
ES (1) ES2163883T3 (en)
FR (1) FR2766716B1 (en)
WO (1) WO1999006079A1 (en)

Cited By (76)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2001082828A2 (en) * 2000-04-28 2001-11-08 Anthony Atala Tissue engineered testicular prosthesis and use thereof
US20020052654A1 (en) * 1999-05-10 2002-05-02 C.R. Bard, Inc. Prosthetic repair fabric
US6447551B1 (en) 1999-03-20 2002-09-10 Aesculap Ag & Co. Kg Flat implant, process for its production and use in surgery
US20030023316A1 (en) * 2000-08-04 2003-01-30 Brown Laura Jean Hybrid biologic-synthetic bioabsorable scaffolds
US20030033021A1 (en) * 2001-07-16 2003-02-13 Plouhar Pamela Lynn Cartilage repair and regeneration scaffold and method
US20030044444A1 (en) * 2001-07-16 2003-03-06 Prasanna Malaviya Porous extracellular matrix scaffold and method
US20030083543A1 (en) * 1999-07-28 2003-05-01 Enrico Nicolo Hernia prosthesis
WO2003041613A1 (en) * 2001-11-14 2003-05-22 Ethicon Gmbh Areal implant
US6592515B2 (en) 2000-09-07 2003-07-15 Ams Research Corporation Implantable article and method
US20040049187A1 (en) * 2000-10-23 2004-03-11 Stuart Burnett Self-adhesive hydratable matrix for topical therapeutic use
US20040054253A1 (en) * 2000-09-07 2004-03-18 Snitkin Eva S. Coated sling material
US20040059431A1 (en) * 2000-08-04 2004-03-25 Plouhar Pamela L. Reinforced small intestinal submucosa
US6723133B1 (en) 1998-09-11 2004-04-20 C. R. Bard, Inc. Performed curved prosthesis having a reduced incidence of developing wrinkles or folds
US6740122B1 (en) 1998-09-11 2004-05-25 C. R. Bard, Inc. Preformed curved prosthesis that is adapted to the external iliac vessels
US20040215231A1 (en) * 2000-02-03 2004-10-28 David Fortune Device for the closure of a surgical puncture
US20040220574A1 (en) * 2001-07-16 2004-11-04 Pelo Mark Joseph Device from naturally occuring biologically derived materials
WO2004093737A1 (en) * 2003-04-17 2004-11-04 Aesculap Ag & Co. Kg Planar implant and surgical use thereof
FR2857851A1 (en) * 2003-07-23 2005-01-28 Cie De Rech En Composants Impl The use of a poly(D,L-lactide-co-glycolide) to produce an anti-adhesion screen on implants used during the surgical repair of ventral ruptures and hernias, especially abdominal wall hernias
US20050113849A1 (en) * 2003-11-26 2005-05-26 Nicholas Popadiuk Prosthetic repair device
US20050244455A1 (en) * 2004-04-20 2005-11-03 Greenawalt Keith E Surgical prosthesis
US20060105026A1 (en) * 2003-04-04 2006-05-18 Fortune David H Tissue-adhesive formulations
US20060128296A1 (en) * 2004-10-29 2006-06-15 Schwan Wade E Intestine processing device and associated method
US20060241622A1 (en) * 2003-06-13 2006-10-26 Zergiebel Earl M Multiple member interconnect for surgical instrument and absorbable screw fastener
US20070032805A1 (en) * 2005-08-03 2007-02-08 Sofradim Production Oxydized cellulose prosthesis
US20070150064A1 (en) * 2005-12-22 2007-06-28 Depuy Spine, Inc. Methods and devices for intervertebral augmentation
US20070150059A1 (en) * 2005-12-22 2007-06-28 Depuy Spine, Inc. Methods and devices for intervertebral augmentation using injectable formulations and enclosures
US20070150063A1 (en) * 2005-12-22 2007-06-28 Depuy Spine, Inc. Devices for intervertebral augmentation and methods of controlling their delivery
US20070286891A1 (en) * 2004-08-03 2007-12-13 Tissuemed Limited Tissue-Adhesive Materials
WO2008006343A1 (en) * 2006-07-13 2008-01-17 Biocer Entwicklungs-Gmbh Modified artificial material
US20080133010A1 (en) * 2003-09-22 2008-06-05 Bartee Chaddick M Hydrophilic high density ptfe medical barrier
US20080147198A1 (en) * 2006-10-19 2008-06-19 C.R. Bard, Inc. Prosthetic repair fabric
US20080281336A1 (en) * 2003-06-13 2008-11-13 Zergiebel Earl M Multiple member interconnect for surgical instrument and absorbable screw fastener
US20090004239A1 (en) * 2007-06-27 2009-01-01 Sebastien Ladet Dural repair material
US20090018575A1 (en) * 2006-03-01 2009-01-15 Tissuemed Limited Tissue-adhesive formulations
US20090036997A1 (en) * 2007-07-30 2009-02-05 Yves Bayon Bioresorbable implant
US20090035858A1 (en) * 2007-07-30 2009-02-05 Yves Bayon Tissue engineering support
US20090036996A1 (en) * 2007-08-03 2009-02-05 Roeber Peter J Knit PTFE Articles and Mesh
US20090068250A1 (en) * 2007-09-07 2009-03-12 Philippe Gravagna Bioresorbable and biocompatible compounds for surgical use
US20090152766A1 (en) * 2007-12-18 2009-06-18 Ethicon, Inc. Methods of making composite prosthetic devices having improved bond strength
US20090187197A1 (en) * 2007-08-03 2009-07-23 Roeber Peter J Knit PTFE Articles and Mesh
WO2010077234A1 (en) * 2008-12-29 2010-07-08 Synthes (U.S.A.) A method of forming and the resulting membrane composition for surgical site preservation
US7819918B2 (en) * 2001-07-16 2010-10-26 Depuy Products, Inc. Implantable tissue repair device
US7871440B2 (en) 2006-12-11 2011-01-18 Depuy Products, Inc. Unitary surgical device and method
US20110027335A1 (en) * 2007-08-10 2011-02-03 Tissuemed Limited Coated medical devices
US7914808B2 (en) 2001-07-16 2011-03-29 Depuy Products, Inc. Hybrid biologic/synthetic porous extracellular matrix scaffolds
US8092529B2 (en) 2001-07-16 2012-01-10 Depuy Products, Inc. Meniscus regeneration device
US8133336B2 (en) 2006-02-03 2012-03-13 Tissuemed Limited Tissue-adhesive materials
US8182545B2 (en) 2000-09-14 2012-05-22 C.R. Bard, Inc. Implantable prosthesis
WO2012123582A1 (en) 2011-03-16 2012-09-20 Sofradim Production Prosthesis comprising a three-dimensional and openworked knit
US20130060334A1 (en) * 2010-02-25 2013-03-07 Orteq B.V. Meniscus repair assembly and method
US8632839B2 (en) 2010-10-19 2014-01-21 Covidien Lp Methods of forming self-supporting films for delivery of therapeutic agents
US8795727B2 (en) 2009-11-09 2014-08-05 Spotlight Technology Partners Llc Fragmented hydrogels
US8920867B2 (en) 2010-10-19 2014-12-30 Covidien Lp Methods of forming self-supporting films for delivery of therapeutic agents
US8932621B2 (en) 2011-10-25 2015-01-13 Covidien Lp Implantable film/mesh composite
US9005308B2 (en) 2011-10-25 2015-04-14 Covidien Lp Implantable film/mesh composite for passage of tissue therebetween
US20150150681A1 (en) * 2012-05-30 2015-06-04 John L. Ricci Tissue repair devices and scaffolds
US9144634B2 (en) 2011-01-14 2015-09-29 Covidien Lp Medical device with intrapore films
US9179994B2 (en) 2011-10-25 2015-11-10 Covidien Lp Implantable film/mesh composite
US9211175B2 (en) 2010-07-08 2015-12-15 Covidien Lp Self-detachable medical devices
US9242026B2 (en) 2008-06-27 2016-01-26 Sofradim Production Biosynthetic implant for soft tissue repair
US9308068B2 (en) 2007-12-03 2016-04-12 Sofradim Production Implant for parastomal hernia
US9364310B2 (en) 2011-07-26 2016-06-14 Covidien Lp Implantable devices including a mesh and a pivotable film
US9445883B2 (en) 2011-12-29 2016-09-20 Sofradim Production Barbed prosthetic knit and hernia repair mesh made therefrom as well as process for making said prosthetic knit
US9499927B2 (en) 2012-09-25 2016-11-22 Sofradim Production Method for producing a prosthesis for reinforcing the abdominal wall
US9510927B2 (en) 2012-06-28 2016-12-06 Sofradim Production Method of making a knit with barbs
US9526603B2 (en) 2011-09-30 2016-12-27 Covidien Lp Reversible stiffening of light weight mesh
US9572907B2 (en) 2010-10-01 2017-02-21 Covidien Lp Implantable polymeric films
US9622843B2 (en) 2011-07-13 2017-04-18 Sofradim Production Umbilical hernia prosthesis
US9700650B2 (en) 2009-11-09 2017-07-11 Spotlight Technology Partners Llc Polysaccharide based hydrogels
US9750837B2 (en) 2012-09-25 2017-09-05 Sofradim Production Haemostatic patch and method of preparation
US9782957B2 (en) 2011-08-24 2017-10-10 Covidien Lp Medical device films
US9801705B2 (en) 2012-06-29 2017-10-31 Sofradim Production Hernia prosthesis
US9839505B2 (en) 2012-09-25 2017-12-12 Sofradim Production Prosthesis comprising a mesh and a strengthening means
US9861590B2 (en) 2010-10-19 2018-01-09 Covidien Lp Self-supporting films for delivery of therapeutic agents
US9867909B2 (en) 2011-09-30 2018-01-16 Sofradim Production Multilayer implants for delivery of therapeutic agents
US9877820B2 (en) 2014-09-29 2018-01-30 Sofradim Production Textile-based prosthesis for treatment of inguinal hernia

Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002009792A1 (en) * 2000-07-28 2002-02-07 Anika Therapeutics, Inc. Bioabsorbable composites of derivatized hyaluronic acid
US6800082B2 (en) 2001-10-19 2004-10-05 Ethicon, Inc. Absorbable mesh device
FR2848118B1 (en) * 2002-12-06 2006-08-11 Textile Hi Tec composite prosthesis
EP2112271A1 (en) * 2008-03-31 2009-10-28 Analytic Biosurgical Solutions - ABISS Association of a film and a hydrogel based on chitosan and his use in surgery
FR2988585B1 (en) 2012-03-28 2015-04-03 Cousin Biotech Plate visceral destiny has laparoscopy

Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4307717A (en) * 1977-11-07 1981-12-29 Lectec Corporation Sterile improved bandage containing a medicament
US4487865A (en) * 1983-12-15 1984-12-11 Biomatrix, Inc. Polymeric articles modified with hyaluronate
US4500676A (en) * 1983-12-15 1985-02-19 Biomatrix, Inc. Hyaluronate modified polymeric articles
US4813942A (en) * 1987-03-17 1989-03-21 Bioderm, Inc. Three step wound treatment method and dressing therefor
WO1989002445A1 (en) 1987-09-18 1989-03-23 Genzyme Corporation Water insoluble derivatives of hyaluronic acid
EP0372969A1 (en) 1988-12-07 1990-06-13 JOHNSON & JOHNSON PATIENT CARE, INC. Low molecular weight heparin, heparinoid and hexuronyl hexosaminoglycan sulfate containing adhesion prevention barrier and process
US5002551A (en) * 1985-08-22 1991-03-26 Johnson & Johnson Medical, Inc. Method and material for prevention of surgical adhesions
WO1992020349A1 (en) 1991-05-20 1992-11-26 Genzyme Corporation Water insoluble derivatives of polyanionic polysaccharides
WO1993011805A1 (en) 1991-12-18 1993-06-24 M.U.R.S.T. Composite membranes for the guided regeneration of tissues
WO1995018638A1 (en) 1994-01-06 1995-07-13 Ed Geistlich Sohne Ag Fur Chemische Industrie Membrane
US5433996A (en) * 1993-02-18 1995-07-18 W. L. Gore & Associates, Inc. Laminated patch tissue repair sheet material
WO1996008277A1 (en) 1994-09-15 1996-03-21 Coletica Use of collagen membranes as peritoneal renewing prostheses
EP0705878A2 (en) 1994-10-06 1996-04-10 Genzyme Corporation Compositions containing polyanionic polysaccharides and hydrophobic bioabsorbable polymers
US5593441A (en) * 1992-03-04 1997-01-14 C. R. Bard, Inc. Method for limiting the incidence of postoperative adhesions
US6056970A (en) 1998-05-07 2000-05-02 Genzyme Corporation Compositions comprising hemostatic compounds and bioabsorbable polymers

Patent Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4307717A (en) * 1977-11-07 1981-12-29 Lectec Corporation Sterile improved bandage containing a medicament
US4487865A (en) * 1983-12-15 1984-12-11 Biomatrix, Inc. Polymeric articles modified with hyaluronate
US4500676A (en) * 1983-12-15 1985-02-19 Biomatrix, Inc. Hyaluronate modified polymeric articles
US5002551A (en) * 1985-08-22 1991-03-26 Johnson & Johnson Medical, Inc. Method and material for prevention of surgical adhesions
US4813942A (en) * 1987-03-17 1989-03-21 Bioderm, Inc. Three step wound treatment method and dressing therefor
WO1989002445A1 (en) 1987-09-18 1989-03-23 Genzyme Corporation Water insoluble derivatives of hyaluronic acid
EP0372969A1 (en) 1988-12-07 1990-06-13 JOHNSON & JOHNSON PATIENT CARE, INC. Low molecular weight heparin, heparinoid and hexuronyl hexosaminoglycan sulfate containing adhesion prevention barrier and process
WO1992020349A1 (en) 1991-05-20 1992-11-26 Genzyme Corporation Water insoluble derivatives of polyanionic polysaccharides
WO1993011805A1 (en) 1991-12-18 1993-06-24 M.U.R.S.T. Composite membranes for the guided regeneration of tissues
US5593441A (en) * 1992-03-04 1997-01-14 C. R. Bard, Inc. Method for limiting the incidence of postoperative adhesions
US5433996A (en) * 1993-02-18 1995-07-18 W. L. Gore & Associates, Inc. Laminated patch tissue repair sheet material
WO1995018638A1 (en) 1994-01-06 1995-07-13 Ed Geistlich Sohne Ag Fur Chemische Industrie Membrane
WO1996008277A1 (en) 1994-09-15 1996-03-21 Coletica Use of collagen membranes as peritoneal renewing prostheses
EP0705878A2 (en) 1994-10-06 1996-04-10 Genzyme Corporation Compositions containing polyanionic polysaccharides and hydrophobic bioabsorbable polymers
US6056970A (en) 1998-05-07 2000-05-02 Genzyme Corporation Compositions comprising hemostatic compounds and bioabsorbable polymers

Cited By (125)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6723133B1 (en) 1998-09-11 2004-04-20 C. R. Bard, Inc. Performed curved prosthesis having a reduced incidence of developing wrinkles or folds
US6740122B1 (en) 1998-09-11 2004-05-25 C. R. Bard, Inc. Preformed curved prosthesis that is adapted to the external iliac vessels
US6447551B1 (en) 1999-03-20 2002-09-10 Aesculap Ag & Co. Kg Flat implant, process for its production and use in surgery
US20020052654A1 (en) * 1999-05-10 2002-05-02 C.R. Bard, Inc. Prosthetic repair fabric
US20030083543A1 (en) * 1999-07-28 2003-05-01 Enrico Nicolo Hernia prosthesis
US20040215231A1 (en) * 2000-02-03 2004-10-28 David Fortune Device for the closure of a surgical puncture
US7727547B2 (en) 2000-04-04 2010-06-01 Tissuemed Limited Tissue-adhesive formulations
WO2001082828A2 (en) * 2000-04-28 2001-11-08 Anthony Atala Tissue engineered testicular prosthesis and use thereof
WO2001082828A3 (en) * 2000-04-28 2002-04-11 Anthony Atala Tissue engineered testicular prosthesis and use thereof
US6620203B2 (en) 2000-04-28 2003-09-16 Anthony Atala Tissue engineered testicular prosthesis and use thereof
US7160333B2 (en) * 2000-08-04 2007-01-09 Depuy Orthopaedics, Inc. Reinforced small intestinal submucosa
US20070129811A1 (en) * 2000-08-04 2007-06-07 Plouhar Pamela L Reinforced small intestinal submucosa
US8366787B2 (en) 2000-08-04 2013-02-05 Depuy Products, Inc. Hybrid biologic-synthetic bioabsorbable scaffolds
US20030023316A1 (en) * 2000-08-04 2003-01-30 Brown Laura Jean Hybrid biologic-synthetic bioabsorable scaffolds
US20040059431A1 (en) * 2000-08-04 2004-03-25 Plouhar Pamela L. Reinforced small intestinal submucosa
US7799089B2 (en) 2000-08-04 2010-09-21 Depuy Orthopaedics, Inc. Reinforced small intestinal submucosa
US20040054253A1 (en) * 2000-09-07 2004-03-18 Snitkin Eva S. Coated sling material
US6592515B2 (en) 2000-09-07 2003-07-15 Ams Research Corporation Implantable article and method
US8905912B2 (en) 2000-09-07 2014-12-09 Ams Research Corporation Implantable article and method
US8702586B2 (en) 2000-09-07 2014-04-22 Ams Research Corporation Implantable article and method
US9022921B2 (en) 2000-09-07 2015-05-05 Ams Research Corporation Implantable article and method
US8147478B2 (en) 2000-09-07 2012-04-03 Ams Research Corporation Coated sling material
US6884212B2 (en) 2000-09-07 2005-04-26 Ams Research Corporation Implantable article and method
US7517313B2 (en) 2000-09-07 2009-04-14 Ams Research Corporation Implantable article and method
US7025063B2 (en) 2000-09-07 2006-04-11 Ams Research Corporation Coated sling material
US9211177B2 (en) 2000-09-07 2015-12-15 Ams Research Corporation Implantable article and method
US8182545B2 (en) 2000-09-14 2012-05-22 C.R. Bard, Inc. Implantable prosthesis
US20040049187A1 (en) * 2000-10-23 2004-03-11 Stuart Burnett Self-adhesive hydratable matrix for topical therapeutic use
US8025896B2 (en) 2001-07-16 2011-09-27 Depuy Products, Inc. Porous extracellular matrix scaffold and method
US8092529B2 (en) 2001-07-16 2012-01-10 Depuy Products, Inc. Meniscus regeneration device
US7819918B2 (en) * 2001-07-16 2010-10-26 Depuy Products, Inc. Implantable tissue repair device
US8337537B2 (en) 2001-07-16 2012-12-25 Depuy Products, Inc. Device from naturally occurring biologically derived materials
US7914808B2 (en) 2001-07-16 2011-03-29 Depuy Products, Inc. Hybrid biologic/synthetic porous extracellular matrix scaffolds
US20040220574A1 (en) * 2001-07-16 2004-11-04 Pelo Mark Joseph Device from naturally occuring biologically derived materials
US20030044444A1 (en) * 2001-07-16 2003-03-06 Prasanna Malaviya Porous extracellular matrix scaffold and method
US20030033021A1 (en) * 2001-07-16 2003-02-13 Plouhar Pamela Lynn Cartilage repair and regeneration scaffold and method
US20030033022A1 (en) * 2001-07-16 2003-02-13 Plouhar Pamela Lynn Cartilage repair and regeneration device and method
US8012205B2 (en) * 2001-07-16 2011-09-06 Depuy Products, Inc. Cartilage repair and regeneration device
US7615065B2 (en) 2001-11-14 2009-11-10 Ethicon Inc. Areal implant
US20050010306A1 (en) * 2001-11-14 2005-01-13 Jorg Priewe Areal implant
WO2003041613A1 (en) * 2001-11-14 2003-05-22 Ethicon Gmbh Areal implant
US20060105026A1 (en) * 2003-04-04 2006-05-18 Fortune David H Tissue-adhesive formulations
US20060116696A1 (en) * 2003-04-17 2006-06-01 Odermatt Eric K Planar implant and surgical use thereof
WO2004093737A1 (en) * 2003-04-17 2004-11-04 Aesculap Ag & Co. Kg Planar implant and surgical use thereof
US9788833B2 (en) 2003-06-13 2017-10-17 Covidien Lp Multiple member interconnect for surgical instrument and absorbable screw fastener
US8292933B2 (en) 2003-06-13 2012-10-23 Tyco Healthcare Group Lp Multiple member interconnect for surgical instrument and absorbable screw fastener
US9364274B2 (en) 2003-06-13 2016-06-14 Covidien Lp Multiple member interconnect for surgical instrument and absorbable screw fastener
US7670362B2 (en) 2003-06-13 2010-03-02 Tyco Healthcare Group Lp Multiple member interconnect for surgical instrument and absorbable screw fastener
US20080281336A1 (en) * 2003-06-13 2008-11-13 Zergiebel Earl M Multiple member interconnect for surgical instrument and absorbable screw fastener
US20060241622A1 (en) * 2003-06-13 2006-10-26 Zergiebel Earl M Multiple member interconnect for surgical instrument and absorbable screw fastener
US20100191294A1 (en) * 2003-06-13 2010-07-29 Tyco Healthcare Group Lp Multiple member interconnect for surgical instrument and absorbable screw fastener
US8926637B2 (en) 2003-06-13 2015-01-06 Covidien Lp Multiple member interconnect for surgical instrument and absorbable screw fastener
US9259221B2 (en) 2003-06-13 2016-02-16 Covidien Lp Multiple member interconnect for surgical instrument and absorbable screw fastener
FR2857851A1 (en) * 2003-07-23 2005-01-28 Cie De Rech En Composants Impl The use of a poly(D,L-lactide-co-glycolide) to produce an anti-adhesion screen on implants used during the surgical repair of ventral ruptures and hernias, especially abdominal wall hernias
US8556989B2 (en) * 2003-09-22 2013-10-15 Chad M. Bartee Hydrophilic high density PTFE medical barrier
US20080133010A1 (en) * 2003-09-22 2008-06-05 Bartee Chaddick M Hydrophilic high density ptfe medical barrier
US20050113849A1 (en) * 2003-11-26 2005-05-26 Nicholas Popadiuk Prosthetic repair device
US20080071300A1 (en) * 2003-11-26 2008-03-20 Nicholas Popadiuk Prosthetic repair device
US8323675B2 (en) 2004-04-20 2012-12-04 Genzyme Corporation Soft tissue prosthesis for repairing a defect of an abdominal wall or a pelvic cavity wall
US20050244455A1 (en) * 2004-04-20 2005-11-03 Greenawalt Keith E Surgical prosthesis
WO2005105172A1 (en) 2004-04-20 2005-11-10 Genzyme Corporation Surgical mesh-like implant
US8460695B2 (en) 2004-04-20 2013-06-11 Genzyme Corporation Making a soft tissue prosthesis for repairing a defect of an abdominal wall or a pelvic cavity wall
US8133504B2 (en) 2004-08-03 2012-03-13 Tissuemed Limited Tissue-adhesive materials
US20070286891A1 (en) * 2004-08-03 2007-12-13 Tissuemed Limited Tissue-Adhesive Materials
US20060128296A1 (en) * 2004-10-29 2006-06-15 Schwan Wade E Intestine processing device and associated method
US20070032805A1 (en) * 2005-08-03 2007-02-08 Sofradim Production Oxydized cellulose prosthesis
US20070150059A1 (en) * 2005-12-22 2007-06-28 Depuy Spine, Inc. Methods and devices for intervertebral augmentation using injectable formulations and enclosures
US20070150063A1 (en) * 2005-12-22 2007-06-28 Depuy Spine, Inc. Devices for intervertebral augmentation and methods of controlling their delivery
US20070150064A1 (en) * 2005-12-22 2007-06-28 Depuy Spine, Inc. Methods and devices for intervertebral augmentation
US8133336B2 (en) 2006-02-03 2012-03-13 Tissuemed Limited Tissue-adhesive materials
US20090018575A1 (en) * 2006-03-01 2009-01-15 Tissuemed Limited Tissue-adhesive formulations
WO2008006343A1 (en) * 2006-07-13 2008-01-17 Biocer Entwicklungs-Gmbh Modified artificial material
US7614258B2 (en) 2006-10-19 2009-11-10 C.R. Bard, Inc. Prosthetic repair fabric
US20080147198A1 (en) * 2006-10-19 2008-06-19 C.R. Bard, Inc. Prosthetic repair fabric
US7900484B2 (en) 2006-10-19 2011-03-08 C.R. Bard, Inc. Prosthetic repair fabric
US7871440B2 (en) 2006-12-11 2011-01-18 Depuy Products, Inc. Unitary surgical device and method
US20090004239A1 (en) * 2007-06-27 2009-01-01 Sebastien Ladet Dural repair material
US8932619B2 (en) 2007-06-27 2015-01-13 Sofradim Production Dural repair material
US20090036997A1 (en) * 2007-07-30 2009-02-05 Yves Bayon Bioresorbable implant
US8198087B2 (en) 2007-07-30 2012-06-12 Sofradim Production Sas Tissue engineering support
US20090035858A1 (en) * 2007-07-30 2009-02-05 Yves Bayon Tissue engineering support
US8834578B2 (en) * 2007-07-30 2014-09-16 Sofradim Production Bioresorbable implant
US20090187197A1 (en) * 2007-08-03 2009-07-23 Roeber Peter J Knit PTFE Articles and Mesh
US20090036996A1 (en) * 2007-08-03 2009-02-05 Roeber Peter J Knit PTFE Articles and Mesh
US20110027335A1 (en) * 2007-08-10 2011-02-03 Tissuemed Limited Coated medical devices
US9750846B2 (en) 2007-09-07 2017-09-05 Sofradim Production Sas Bioresorbable and biocompatible compounds for surgical use
US20090068250A1 (en) * 2007-09-07 2009-03-12 Philippe Gravagna Bioresorbable and biocompatible compounds for surgical use
US9308068B2 (en) 2007-12-03 2016-04-12 Sofradim Production Implant for parastomal hernia
US8206632B2 (en) 2007-12-18 2012-06-26 Ethicon, Inc. Methods of making composite prosthetic devices having improved bond strength
US20090152766A1 (en) * 2007-12-18 2009-06-18 Ethicon, Inc. Methods of making composite prosthetic devices having improved bond strength
US9242026B2 (en) 2008-06-27 2016-01-26 Sofradim Production Biosynthetic implant for soft tissue repair
US9289538B2 (en) 2008-12-29 2016-03-22 DePuy Synthes Products, Inc. Method of forming and the resulting membrane composition for surgical site preservation
WO2010077234A1 (en) * 2008-12-29 2010-07-08 Synthes (U.S.A.) A method of forming and the resulting membrane composition for surgical site preservation
US8748508B2 (en) 2008-12-29 2014-06-10 DePuy Synthes Products, LLC Method of forming and the resulting membrane composition for surgical site preservation
US9700650B2 (en) 2009-11-09 2017-07-11 Spotlight Technology Partners Llc Polysaccharide based hydrogels
US9592299B2 (en) 2009-11-09 2017-03-14 Spotlight Technology Partners Llc Hydrogel compositions
US9861701B2 (en) 2009-11-09 2018-01-09 Spotlight Technology Partners Llc Hydrogel compositions
US8795727B2 (en) 2009-11-09 2014-08-05 Spotlight Technology Partners Llc Fragmented hydrogels
US9289449B2 (en) 2009-11-09 2016-03-22 Spotlight Technology Partners Llc Hydrogel compositions
US20130060334A1 (en) * 2010-02-25 2013-03-07 Orteq B.V. Meniscus repair assembly and method
US9211175B2 (en) 2010-07-08 2015-12-15 Covidien Lp Self-detachable medical devices
US9572907B2 (en) 2010-10-01 2017-02-21 Covidien Lp Implantable polymeric films
US8920867B2 (en) 2010-10-19 2014-12-30 Covidien Lp Methods of forming self-supporting films for delivery of therapeutic agents
US9861590B2 (en) 2010-10-19 2018-01-09 Covidien Lp Self-supporting films for delivery of therapeutic agents
US8632839B2 (en) 2010-10-19 2014-01-21 Covidien Lp Methods of forming self-supporting films for delivery of therapeutic agents
US9642946B2 (en) 2011-01-14 2017-05-09 Covidien Lp Medical device with intrapore films
US9144634B2 (en) 2011-01-14 2015-09-29 Covidien Lp Medical device with intrapore films
WO2012123582A1 (en) 2011-03-16 2012-09-20 Sofradim Production Prosthesis comprising a three-dimensional and openworked knit
US9554887B2 (en) 2011-03-16 2017-01-31 Sofradim Production Prosthesis comprising a three-dimensional and openworked knit
US9622843B2 (en) 2011-07-13 2017-04-18 Sofradim Production Umbilical hernia prosthesis
US9364310B2 (en) 2011-07-26 2016-06-14 Covidien Lp Implantable devices including a mesh and a pivotable film
US9782957B2 (en) 2011-08-24 2017-10-10 Covidien Lp Medical device films
US9867909B2 (en) 2011-09-30 2018-01-16 Sofradim Production Multilayer implants for delivery of therapeutic agents
US9526603B2 (en) 2011-09-30 2016-12-27 Covidien Lp Reversible stiffening of light weight mesh
US9005308B2 (en) 2011-10-25 2015-04-14 Covidien Lp Implantable film/mesh composite for passage of tissue therebetween
US9179994B2 (en) 2011-10-25 2015-11-10 Covidien Lp Implantable film/mesh composite
US8932621B2 (en) 2011-10-25 2015-01-13 Covidien Lp Implantable film/mesh composite
US9445883B2 (en) 2011-12-29 2016-09-20 Sofradim Production Barbed prosthetic knit and hernia repair mesh made therefrom as well as process for making said prosthetic knit
US20150150681A1 (en) * 2012-05-30 2015-06-04 John L. Ricci Tissue repair devices and scaffolds
US9510927B2 (en) 2012-06-28 2016-12-06 Sofradim Production Method of making a knit with barbs
US9801705B2 (en) 2012-06-29 2017-10-31 Sofradim Production Hernia prosthesis
US9839505B2 (en) 2012-09-25 2017-12-12 Sofradim Production Prosthesis comprising a mesh and a strengthening means
US9750837B2 (en) 2012-09-25 2017-09-05 Sofradim Production Haemostatic patch and method of preparation
US9499927B2 (en) 2012-09-25 2016-11-22 Sofradim Production Method for producing a prosthesis for reinforcing the abdominal wall
US9877820B2 (en) 2014-09-29 2018-01-30 Sofradim Production Textile-based prosthesis for treatment of inguinal hernia

Also Published As

Publication number Publication date Type
EP0998313B1 (en) 2001-08-22 grant
EP0998313A1 (en) 2000-05-10 application
FR2766716A1 (en) 1999-02-05 application
WO1999006079A1 (en) 1999-02-11 application
DE69801442D1 (en) 2001-09-27 grant
ES2163883T3 (en) 2002-02-01 grant
FR2766716B1 (en) 2000-02-18 grant
DE69801442T2 (en) 2001-12-06 grant

Similar Documents

Publication Publication Date Title
US3526228A (en) Collagen lamina dural prosthesis
US5676698A (en) Soft tissue implant
DeBord The historical development of prosthetics in hernia surgery
Barnes et al. Nanofiber technology: designing the next generation of tissue engineering scaffolds
US6408656B1 (en) Isoelastic prosthetic filet stitch fabric
US5263984A (en) Prosthetic ligaments
US6398814B1 (en) Bioabsorbable two-dimensional multi-layer composite device and a method of manufacturing same
US3736646A (en) Method of attaching surgical needles to multifilament polyglycolic acid absorbable sutures
US5632776A (en) Implantation materials
US6703041B2 (en) Compositions containing polyanionic polysaccharides and hydrophobic bioabsorbable polymers
US7252837B2 (en) Hemostatic wound dressing and method of making same
US20090005867A1 (en) Mesh implant
US5879359A (en) Biodegradable guide channels comprised of esters of hyaluronic acid for use in tissue repair as surgical aids
US20030023316A1 (en) Hybrid biologic-synthetic bioabsorable scaffolds
US5700477A (en) Bioabsorbable wound implant materials
US3366440A (en) Process for manufacturing a collagen fabric-film laminate
US20050283255A1 (en) Tissue-derived mesh for orthopedic regeneration
US5565210A (en) Bioabsorbable wound implant materials
US6391939B2 (en) Collagenic material useful in particular for preventing post-operative adhesions
US20110257761A1 (en) Prosthetic device having regions of varying stretch and method of manufacturing the same
US6136024A (en) Artificial blood vessel
US6162247A (en) Vascular graft impregnated with a heparin-containing collagen sealant
US20070280990A1 (en) Anti-Adhesion Barrier
US5211661A (en) Artificial living body composite material
US20090018655A1 (en) Composite Implant for Surgical Repair

Legal Events

Date Code Title Description
AS Assignment

Owner name: SOFRADIM PRODUCTION, FRANCE

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:ORY, FRANCOIS REGIS;THERIN, MICHEL;REEL/FRAME:009924/0255

Effective date: 19990319

AS Assignment

Owner name: SOFRADIM PRODUCTION, FRANCE

Free format text: CHANGE OF ADDRESS W/PARTIAL TRANSLATION;ASSIGNOR:SOFRADIM PRODUCTION;REEL/FRAME:011783/0918

Effective date: 20010307

FPAY Fee payment

Year of fee payment: 4

FPAY Fee payment

Year of fee payment: 8

FPAY Fee payment

Year of fee payment: 12